Contrast Agent Imaging With Agent Specific Ultrasound Detection

ABSTRACT

Highly specific measurements of flow in vessels, such as the coronary artery, can be obtained by processing cubic fundamental information. By showing flow in vessels with a high degree of contrast-to-tissue specificity, ultrasound based 3D contrast agent based coronary artery angiograms may be possible. Measurement and display of the velocity of agent from the cubic fundamental signal is provided simultaneously with display of cubic fundamental energy, such as providing a display map indexed by both energy and velocity. High pulse repetition frequency (PRF) for cubic fundamental detection in conjunction with long velocity measurement intervals may increase low velocity sensitivity and measurement precision. Pulsed wave (PW) Doppler may be improved by using a cubic fundamental sensitive pulse sequence. Using cubic fundamental sensitive techniques with other motion estimation techniques, such as two-dimensional velocity estimation or speckle tracking, may operate better than using other contrast agent detection techniques because of substantially reduced clutter.

CROSS-REFERENCE TO RELATED APPLICATIONS

The present patent document is a divisional of co-pending U.S. patentapplication Ser. No. 11/152,521 filed Jun. 14, 2005, which is adivisional of U.S. Pat. No. 7,004,906 (application Ser. No. 10/899,803,filed Jul. 26, 2004), which are hereby incorporated by reference.

BACKGROUND

This present invention relates to contrast agent imaging. In particular,the cubic fundamental response provides agent specific ultrasoundimaging.

Information at the cubic fundamental is detected by varying the transmitamplitude and phase associated with combined echo signals. Sometechniques for detecting cubic fundamental information are disclosed inU.S. Pat. Nos. 6,494,841, 6,602,195, 6,632,177 and 6,682,482, thedisclosures of which are incorporated herein by reference. The cubicfundamental information is highly specific to ultrasound contrast agentssince contrast agents produce cubic response and the transducer andtissue produce very little cubic response. The information providestissue clutter rejection, allowing for imaging more specific to contrastagents. For example, small vessels within tissue may be more easilyimaged or identified using cubic fundamental information.

U.S. Pat. No. 6,638,228, the disclosure of which is incorporated hereinby reference, provides for contrast-agent enhanced color-flow imaging.Power modulation or amplitude variation of the transmit pulses is usedto obtain cubic fundamental information. A color Doppler estimator isused to detect the cubic fundamental information for imaging.

BRIEF SUMMARY

By way of introduction, the preferred embodiments described belowinclude a method and systems for contrast agent imaging with ultrasound.Highly specific measurements of flow in vessels such as the coronaryartery can be obtained by processing cubic fundamental information. Byshowing flow in vessels with a high degree of specificity, ultrasoundbased 3D contrast agent based coronary artery angiograms may bepossible. The depiction of vessels in the liver, in particular theirdirection, is of great clinical interest during contrast agent exams.These and other applications may be available by improving flowestimation from or imaging of cubic fundamental information.

Different techniques for contrast agent imaging with cubic fundamentalinformation are discussed herein. Measurement and display of thevelocity of agent from the cubic fundamental signal is providedsimultaneously with display of cubic fundamental energy, such asproviding a display map indexed by both energy and velocity. High pulserepetition frequency (PRF) for cubic fundamental detection inconjunction with long velocity measurement intervals may increase lowvelocity sensitivity and measurement precision. Pulsed wave (PW) Dopplermay be improved by using a cubic fundamental sensitive pulse sequence.Using cubic fundamental sensitive techniques with other motionestimation techniques, such as two-dimensional velocity estimation orspeckle tracking, may operate better than using other contrast agentdetection techniques because of substantially reduced clutter.

The techniques summarized above and/or disclosed below are used alone orin any possible combination. The present invention is defined by thefollowing claims, and nothing in this section should be taken as alimitation on those claims. Further aspects and advantages of theinvention are discussed below in conjunction with the preferredembodiments and may be later claimed independently or in combination.

BRIEF DESCRIPTION OF THE DRAWINGS

The components and the figures are not necessarily to scale, emphasisinstead being placed upon illustrating the principles of the invention.Moreover, in the figures, like reference numerals designatecorresponding parts throughout the different views.

FIG. 1 is a block diagram of one embodiment of a system for contrastagent ultrasound imaging with cubic fundamental information;

FIG. 2 is a flow chart diagram of one embodiment of a method forcontrast agent ultrasound imaging with cubic fundamental information;

FIG. 3 is a graphic representation of a display map indexed by cubicfundamental based velocity and energy;

FIG. 4 is a flow chart diagram of another embodiment of a method forcontrast agent ultrasound imaging with cubic fundamental information;

FIG. 5 is a frequency response plot of one embodiment of a contrastpulse sequence acquisition pattern;

FIG. 6 is a flow chart diagram of yet another embodiment of a method forcontrast agent ultrasound imaging with cubic fundamental information;

FIG. 7 is a graphical representation of a cross beam method fordetermining a two-dimensional velocity; and

FIG. 8 is a graphical representation of a speckle search method.

DETAILED DESCRIPTION OF THE DRAWINGS AND PRESENTLY PREFERRED EMBODIMENTS

Obtaining cubic fundamental information is disclosed in U.S. Pat. No.6,494,841. Any of the transmit sequences and receive combinationsdisclosed therein may be used for obtaining cubic fundamentalinformation for use with the flow imaging described below. Othertransmit sequences and receive combinations for obtaining cubicfundamental information may be used, such as disclosed in U.S. Pat. Nos.6,602,195, 6,632,177, 6,638,228 and 6,682,482. In general, a sequence ofpulses with different amplitudes and phases are transmitted. Usingamplitude change or different amplitudes without different phases mayalso be used to obtain cubic fundamental information. By combiningreceived signals responsive to the sequence, a sample including cubicfundamental information is obtained. Velocity, energy or other flowparameters may be estimated from a plurality of the samples. The clutteror tissue rejection of the cubic fundamental information may beadvantageously used in flow imaging of contrast agents.

FIG. 1 shows a system 10 for contrast agent imaging with ultrasound. Thesystem 10 includes a beamformer 12, a beamformer controller 13, atransducer 14, a detector 16, a memory 18 and a display 20. Additional,different or fewer components may be provided, such as the system 10without the memory 18 or with a scan converter or additional detectors.The system 10 is a medical diagnostic ultrasound imaging system in oneembodiment, but other imaging systems of the same or different modality(ultrasound) may be used. The system 10 implements contrast pulsesequences (CPS) for obtaining information at the cubic fundamental.

The beamformer 12 is an ultrasound transmitter, transmit beamformer,receive beamformer, summer, filter, analog circuit, digital circuit orcombinations thereof. The beamformer 12 is operable to obtain ultrasounddata representing a cubic fundamental response. The beamformer 12transmits a sequence of pulses associated with a given scan line, suchas all the pulses along the line or the pulses along the scan line andadjacent scan lines. Responsive echoes are received. The beamformer 12generates ultrasound data for each receive beam. By combining receivebeams responsive to different ones of the pulses, cubic fundamentalinformation is obtained.

The transmit sequence is controlled to generate echo signals responsiveto the cubic fundamental. The beamformer 12 is operable to transmit aplurality of pulses having at least two different amplitude levels andat least two of the plurality of pulses having opposite phases. Anultrasonic transmitter that is coupled to the transducer 14 by atransmit/receive switch. The transmitter applies transmit signals ofselected waveform timing and phasing to the individual elements of thetransducer 14. In response, the transducer 14 creates ultrasonicpressure waves, which conventionally are focused along one or more scanlines L1, L2. In the conventional manner, scan lines L1, L2 are steeredacross the region of interest by properly adjusting the phase and timedelays of the transmit waveforms. Scatterers in the region of interestreturn ultrasonic energy to the transducer 14, which in response formsecho signals that are applied by the transmit/receive switch to areceiver. The receiver applies appropriate phase and/or time delays toindividual receive signals to cause the receive signals to addcoherently from desired locations within the region of interest.

The transmitter, transducer 14 and receiver can take any desired forms.The widest variety of techniques can be used to implement thetransmitter, including both analog and digital techniques. The followingU.S. patents, all assigned to the assignee of the present invention,provide examples of the types and approaches that can be used toimplement the transmitter: U.S. Pat. Nos. 4,550,607, 4,699,009,5,148,810, 5,608,690, and 5,675,554. If desired, the transmitter may beused to form unfocused or only slightly focused pressure waves in theregion of interest. These examples are of course not intended to belimiting in any way.

Similarly, the transducer 14 can take any desired form. The transducer14 can be a 1-, 1.25-, 1.5-, 1.75- or 2-dimensional array ofpiezoelectric or capacitive membrane elements. By way of example, thetransducers described in any of the following U.S. patents (all assignedto the assignee of the present invention) can readily be adapted for usewith this invention: U.S. Pat. Nos. 5,261,408, 5,297,533, 5,410,208,5,415,175, 5,438,998, 5,562,096, 5,657,295, 5,671,746, 5,706,820,5,757,727, 5,792,058, 5,916,169, and 5,920,523. Once again, this list isnot intended to be limiting, and any suitable transducer array can beused.

The receiver can include beamformers implemented using any suitabletechnology. For example, the beamformers described in the following U.S.patents (all assigned to the assignee of the present invention) canreadily be adapted for use with this invention: U.S. Pat. Nos.4,550,607, 4,699,009, and 5,555,534. Alternately, the receiver caninclude one or more beamformers that form beams on a point-by-pointbasis rather than a scan-line basis. As before, these examples are notintended to be limiting.

As described above, the amplitude and phase of transmitted signals arecontrolled to provide the desired contrast pulse sequence. In the system10, the beamformer controller 13, such as a transmitter power and phasecontrol, applies control signals to the beamformer 12 to create transmitpulses of the desired power and phase. Transmitter power can be variedin any suitable manner, as for example by adjusting the voltage appliedto individual transducer elements, or by adjusting the number oftransducer elements (or transmit aperture) used to form a particularpulse.

For obtaining ultrasound data at the cubic fundamental, the beamformer12 includes line memories and a summer or a filter to combine signalsresponsive to the transmission of the CPS. Beamformed signals from thereceiver are stored in the line memories or filter buffers. The linememories or buffers can be formed as physically separate memories, oralternately they can be formed as selected locations in a commonphysical device. The beamformed signals for a given CPS are stored inthe line memories or buffers and then weighted and summed in a weightedsummer. The weighted summer is controlled by the beamformer controller13, such as a receive amplitude and phase weighting control, thatprovides the weighting values for both amplitude and phase that are usedin the weighted summer. The memories and the summer can be implementedusing analog or digital techniques. The weighted summer forms acomposite output signal by weighting the separate beamformed receivesignals in any of the ways described below. The composite output signalfor a given spatial location is a sample associated with the cubicfundamental response.

In the foregoing example, the composite output signal was formed from aweighted summation of receive signals that had been beamformed. Theweighted summation can be performed at baseband, IF or RF and prior toor after beamforming. Similarly, the weighted summation can be performedeither before or after scan conversion.

The detector 16 is a B-mode detector, Doppler detector, pulsed waveDoppler detector, correlation processor, Fourier transform processor,application specific integrated circuit, general processor, controlprocessor, field programmable gate array, digital signal processor,analog circuit, digital circuit, combinations thereof or other now knownor later developed device for detecting information for display frombeamformed ultrasound samples. In one embodiment, the detector 16implements a fast Fourier transform from a plurality of samplesrepresenting a same region or gate location. Each of the samples isresponsive to cubic fundamental so that a pulsed wave Doppler displaymay be generated from cubic fundamental information.

In another embodiment, the detector 16 is operable to estimate velocity,direction, and energy values as a function of the ultrasound data orsamples. Two or more samples or combined signals responsive to the CPSpulses are input to the detector 16. The detector 16 determines thefirst and second coefficients of an auto-correlation function. The firstorder coefficient estimates energy, and the second order coefficientestimates velocity. Direction is derived from the velocity values byretaining the sign and removing the magnitude. Other calculations toestimate velocity and/or energy may be used, such as a cross-correlationor transform.

The memory 18 is a look-up table, buffer, random access memory, readonly memory, combinations thereof or other now known or later developeddevice for storing data or a look-up table. The memory 18 is operable tostore a display map. The display map may take many forms, such asseparate display maps for either of energy or velocity. In oneembodiment, the display map is indexed by both the velocity and energyvalues for outputting a display value. For example, the display mapoutputs a color value distinguishing between different energies ordifferent velocities. A color value for one of the energy or velocityvalues for a spatial location is output as a function of the energyinput. The color values representing velocity are displayed for higherenergy, and the color values representing energy are displayed for lowerenergy. Color values representing energy are displayed for low velocityregardless of the energy level. The color values for energy arenon-directional color coded, and the color values for velocity aredirectional color coded. Any threshold may be used for switching betweenthe energy and velocity output values. In an alternative embodiment, aprocessor calculates the display values from one or more input sourcesof data.

The display 20 is a CRT, monitor, LCD, flat panel, projector or otherdisplay device. The display 20 receives display values for displaying animage. The display values are formatted as a one dimensional image, twodimensional image or a three dimensional representation. In oneembodiment, the display values correspond to a PW Doppler image showinga range of frequencies modulated by energy as a function of time for oneor more spatial locations. In another embodiment, the display valuescorrespond to energy and/or velocity information for each spatiallocation. In yet other embodiments, B-mode, M-mode, velocity, energy,variance, contrast agent, harmonic or other types of images aredisplayed. The images are responsive, at least in part, to cubicfundamental information.

FIG. 2 shows one embodiment of a method for contrast agent imaging withultrasound. Additional, different or fewer acts may be provided. Forexample, the acts of the methods of FIGS. 4 and/or 6 are performed alongwith the acts of FIG. 2. As another example, velocity estimatesresponsive to cubic fundamental transmissions are obtained in acts 30and 32 without performing acts 34 and 36. As yet another example, cubicfundamental velocity estimates are obtained in act 32 without the longpulse repetition interval (PRI) and high sampling rate CPS pulses of act30. The method of FIG. 2 is implemented using the system of FIG. 1 oranother system.

In act 30, a sequence of pulses is transmitted (TX) for CPS. Thesequence of pulses is transmitted along or adjacent to a scan line, L1.The sequence of pulses is used to form a plurality of samples forestimating velocity of contrast agent as a function of the cubicfundamental of the echo signals. The velocity is responsive to echoesfrom each of the pulses of the sequence.

Cubic fundamental signals can be obtained by transmitting an exemplarythree pulses with varying amplitude and phase. A plurality of pulseshaving at least two different amplitude levels and at least two of theplurality of pulses having opposite phases are transmitted. For example,the sequence of pulses to obtain cubic fundamental information for asingle sample for each depth location along a line is represented as [½−1 ½]. The magnitude (i.e., ½ versus 1) represents amplitude and thepolarity (i.e., negative versus positive) represents the relativephasing, here a 180 degree difference. [½ 1 ½] as well as othersequences with or without polarity changes or with different amplitudedifferences may also be used. It is preferred that the ½ amplitudepulses are achieved by using a subset of the full aperture, such as evenor odd elements of the aperture, so may be represented as ½e for theeven elements and ½o for the odd elements. Other aperture groupings toobtain the desired amplitude may be used.

A sample is formed by combining signals responsive to the transmittedpulses. In one embodiment, the signals for each pulse are equallyweighted and summed, but unequal weighting with or without phase shiftsmay be performed for the combination of received signals. A sample isrepresented as Y_(N). Each sample is formed from a unique combination.In one embodiment, the transmit pulses used for a given sample are usedonly for that sample. Alternatively, one or more pulses are used fordifferent samples. Table 1 shows a contrast pulse transmit sequencealong one scan line with receive filtering using shared pulses.

TABLE 1 Transmit sequence ½ e −1 ½ o −1 ½ e Received point X₀ X₁ X₂ X₃X₄ Receive weight Y₀ 1 1 1 Receive weight Y₁ 1 1 1 Receive weight Y₂ 1 11The X_(n) corresponds to the order of transmission of the five pulsesalong the scan line. The “1” values are the weights applied to receivesignals. The location of the “1” corresponds to the transmit pulses andassociated received signals to be weighted. In table 1, three sets ofsamples Y₀, Y₁ and Y₂ for a same scan line are output.

The three samples are output from the filter block into the detector,such as a color Doppler autocorrelation detection processor. Thevelocity is estimated in act 32 as a function of the three samples orcombined signals.

The Y₁ samples of Table 1 may have poor linear fundamental rejection,and may contaminate the detected agent energy and velocity estimates.The input receive signals may be reordered for input to a fixed clutterfilter, and color Doppler detection performed with two desired points.Table 2 represents using the same transmit sequence, but reordering theresulting received signals for combination into two sets of samples.

TABLE 2 Transmit sequence ½ e ½ o −1 −1 ½ e Received point X₀ X₂ X₃ X₁X₄ Receive weight Y₀ 1 1 0 1 Receive weight Y₁ 1 1 0 1Alternative methods to discard or avoid the undesired output samplesinclude decimation filtering and generalized matrix filtering. Otherdesired combinations responsive to cubic fundamental information inputto the autocorrelation operation may be used.

There are many sequences that can be used to compute cubic fundamentalsensitive contrast agent velocity. Additional points can be added to thesequences to improve the quality of the velocity estimates, such asshown in table 3.

TABLE 3 Est. reorder Transmit sequence Clutter filter samples pattern ½e−1½o −1½e [1 0 1 1] 2 0, 2, 3, 1, 4 ½e −1½o ½e [1 0 1 0 1] 2 0, 2, 4, 1,3, 5 −1½o ½e −1½o ½e [1 0 0 1 0 0 1] 3 0, 3, 6, 1, 4, 7, 2, −1½o ½e −1½o5, 8 ½e 1½o 1½e [−1 0 1 1] 2 0, 2, 4, 1, 3In table 3, the estimate samples represent the number of sets ofcombined signals or samples output for velocity estimation. The clutterfilter represents the weighting for a moving window applied to thereceived signals of the CPS transmit pulses to obtain the samples. Thereorder pattern is provided to present the desired data to the clutterfilter for forming the samples. Other orders may be used.

Sequences may be adapted to provide improved sensitivity for lowvelocities in act 30. The pulses are spaced unequal distances apart intime within the sequence. For example, pulses for detection of cubicfundamental information are transmitted closer together in time thanpulse sets for estimation of the velocity. Since different transmittedpulses are used for different samples, the sequence of pulses along aline or adjacent lines may provide pulses used for each sample at a highrate (i.e., relatively close spacing in time), but with the pulsesdifferent samples used for velocity estimation spaced apart in time.

In one embodiment, the spatial distribution of pulses of a sequence isobtained by interleaving pulses for other sequences. For example, pulsesof a sequence used for forming samples on different, such as adjacent,scan lines are transmitted interleaved with pulses for a given scanline. The interleaving provides for a different number of pulses fromother sequences being between two different sequential pairs of thepulses of a given sequence, resulting in variation of the time betweenpulses of the given sequence where a sequence is associated with pulsesfor two or more samples to be used for estimating a velocity.

In one embodiment for interleaving, equal spacing in time between thepulses is used. This interleaving is similar to interleaving for lowvelocity scale settings for conventional color Doppler. For example, ifthe flow sample interleave ratio (FSIR) is 3 (i.e., data for threespatially distinct scan lines are acquired in an interleaved fashion)and the sample count (i.e., number of pulses per scan line) is 6, thenthe total of 18 firings are acquired with the following ordering:

By convention, the PRI is defined as the time interval between pulsesfor the same spatial location. It corresponds to the velocity scale setby the user. A 6 pulse contrast pulse sequence with the sameinterleaving sequence showing the aperture weighting pattern is providedas:

1^((1/2) e) 2^((1/2) e) 3^((1/2) e) 1⁽⁻¹⁾ 2⁽⁻¹⁾ 3⁽⁻¹⁾ 1^((1/2O))2^((1/2O)) 3^((1/2O)) 1^((1/2) e) 2^((1/2) e) 3^((1/2) e) 1⁽⁻¹⁾ 2⁽⁻¹⁾3⁽⁻¹⁾ 1^((1/2O)) 2^((1/2O)) 3^((1/2O))

The time between individual firings is PRI/3, or more generallyPRI/FSIR.

By acquiring contrast pulse sequences with a long PRI, the velocityresolution for low velocities is increased. For example, the samplecorrelation is between complex clutter filter output samples that are3*PRI apart in time. Sensitivity to linear fundamental clutter may beincreased in the interleaving cases as well as the possibility ofincoherence due to motion within the three pulses of the coherentlycombined CPS triplet (i.e., three pulses used to form one set of samplesalong a scan line) because of the longer PRI. To avoid this unwantedsensitivity, the pulses used for a given sample are maintained closer intime, providing unequal temporal spacing of pulses of the sequence. Forexample, at least six first pulses are transmitted. The six pulsescorrespond to two triplets or two sets of CPS pulses where each set hasat least two pulses with different amplitude levels and at least twopulses with different phases. Three pulses (i.e., a first triplet) inthe sequence corresponding to a first set of samples are transmittedfree of interleaving. Pulses for one or more other sequences are thantransmitted. Then, three more pulses (i.e., a second triplet) in theoriginal sequence corresponding to a second set of samples aretransmitted free of interleaving. This example sequence is representedby:

This example sequence preserves high sampling rates for the CPS tripletswhile retaining the long correlation intervals for velocity sensitivity.Good linear fundamental clutter rejection is maintained because thesecond difference clutter filtering in this example is performed at ahigh sample rate (PRI/3). Increased velocity resolution is provided bythe sample interleaving because the autocorrelation is performed acrosssamples that are 3*PRI apart in time. Stationary and moving contrastagent may be better differentiated because of the greater velocityresolution.

In alternative embodiments, sets of four or more pulses are used insteadof triplets (i.e., sets of three pulses) to acquire a given sample. Inyet other embodiments, some interleaving is provided within the tripletor set of pulses for combination to obtain the cubic fundamentalinformation. More or less relative interleaving is provided between thesets of pulses than shown in the example above or than used within thesets or triplets. In one embodiment, the pulses of a set used forobtaining cubic fundamental information are interleaved with another setin the same sequence. In yet another alternative embodiment, one or morepulses of a sequence are used for generating two or more samples.

Received signals responsive to each set of transmitted pulses arecombined. The combination is performed as discussed above to obtain asample or samples along a scan line responsive to cubic fundamentalinformation. Received signals responsive to the different amplitude andphased pulses are combined to obtain cubic fundamental information. Inthe example above, received signals responsive to the first triplet(i.e., the first three pulses labeled “1”) are combined, and thereceived signals responsive to the second triplet (i.e., the last threepulses labeled “1”) are combined. By combining the received signals foreach of the two or more sets of pulses in a sequence, two or moresamples are generated for each given spatial location.

Velocities are estimated as a function of cubic fundamental signalsresponsive to the pulses of the sequence. The velocity at a givenspatial location is estimated from the two or more samples formed fromthe sequence of transmit pulses. For example, a velocity is estimatedfrom the two samples obtained using the “1” sequence transmit pulses inthe example above.

In act 34, an energy of contrast agent is obtained. The energy isobtained as a function of a cubic fundamental of ultrasound signals. Forexample, a CPS sequence using all the same, all different or a sub-setof transmit pulses used to estimate velocity is transmitted. Usingdifferent pulses may result in received signals responsive to the sameor different contrast agent due to movement of the contrast agent. Asingle sample or a plurality of samples is used to estimate the energy.

In act 36, an image is generated as a function of both the velocity andenergy estimates. Calculations, processes or look-up table maps may beused for identifying display values for the image. The image is a blackand white or color image. In one embodiment, a color map or look-uptable indexed by the velocity and energy values is used to generatedisplay values. FIG. 3 shows one such color map. One of the energy orvelocity is displayed for a spatial location as a function of theenergy. The velocity is displayed for higher energy, and the energy isdisplayed for lower energy. The velocity is a color, such as adirectional color coded display value. For higher velocities, adifferent shade, brightness or hue is displayed. A different shade,brightness or hue is used to distinguish negative from positivevelocities. For energies, a non-directional color coded display value isgenerated. The display values for energy are a different color, shade,hue or brightness than the display values for velocity. Low energysignals are shown without unreliable velocity estimates with anon-directional color coding. High energy signals with more reliablevelocity estimates show a color-coded velocity.

The threshold or cut-off between displaying energy or velocityinformation is set by experimentation or in response to user input. Inone region associated with stationary contrast agent, spatial locationsassociated with a sufficiently low velocity are displayed as black, asenergy or as a non-velocity regardless of the energy level.

The map is used for each of a plurality of spatial locations to generatedisplay values for a color image. The map can also be changed to showblack (or the underlying tissue or B-mode in mix modes) in the locationswhere velocity is not mapped and/or stationary agent is located. Thecolor mapping scheme then appears very much like a color Doppler mapwhere stationary agent is suppressed. Alternatively, stationary agent ismapped to a color different from moving agent while the absence of agentis mapped to black or underlying B-mode. The map may be simplified toshow only directional information rather than velocity. Any of themapping or combinations shown in U.S. Pat. No. 6,177,923, the disclosureof which is incorporated herein by reference, can be applied here.

For imaging small vessels, signals associated with tissue velocity maybe subtracted from velocities associated with both tissue and contrastagent velocities. Measurement of contrast agent flow velocities invessels while inside moving tissue could allow vessels to be shown withhigh contrast despite the presence of perfused contrast agent in thetissues. Tissue velocity is determined using received signals withoutcombination to find the cubic fundamental response. For example, tissuevelocity is estimated from received signals for a sub-set of fewer thanall of the pulses used in CPS. Using the 6-pulse sequence arranged astwo identical 3 pulse triplets [½e −1 ½o] discussed above, the contrastand tissue agent velocity is provided by correlating across thetriplets. The fundamental signal tissue velocity is obtained bycorrelating across the two full amplitude signals. In table 4 below, thecomplex filter output samples Y₀ and Y₁ yield the combined agent flowand tissue velocity measurement Vat. The samples Z₀ and Z₁ yield thetissue velocity measurement V_(t).

TABLE 4 Transmit sequence ½ e ½ e −1 −1 ½ o ½ o Received point X₀ X₃ X₁X₄ X₂ X₅ Receive weight Y₀ 1 0 1 0 1 Receive weight Y₁ 1 0 1 0 1 Receiveweight Z₀ 0 0 1 0 0 Receive weight Z₁ 0 0 1 0 0Alternatively, the tissue velocity is estimated from pulses not alsoused for estimating velocity.

The velocity estimates are obtained in parallel. Alternatively, one ormore passes are performed through a same device to obtain the estimatessequentially from the same or different data.

To identify the velocity and contrast agents within a vessel, the tissuevelocity is removed from the contrast agent and tissue velocity. Theactual contrast agent flow velocity V_(a) can be derived by subtractingthe tissue velocity measurement V_(t) from the combined agent and tissuevelocity V_(at). Alternatively, the input spectrum of the agent velocitymeasurement is modulated based on the tissue velocity measurementsimilar to adaptive clutter filtering. The tissue information is movedto 0, or zero velocity, so that the vessel contrast agent velocityremains. The information at and around 0 is then removed by clutterfiltering.

The ½e and ½o pulses may also be used to help improve the quality of thetissue velocity estimate thru variance reduction, providing moreaveraged velocities. These pulses may have poor quality grating lobeperformance where the reduction in amplitude is obtained by partiallysampling the aperture. Combining these pulses coherently could improvegrating lobe performance, but may introduce a zero in the amplitudefrequency response of the tissue velocity estimator for high velocities.

Fundamental and/or second harmonic clutter velocity bias may be rejectedby modulating the relative phases of the triplets or other groupings ofpulses. The transmit phases are modulated to affect the velocityestimator to achieve improved velocity based detection specificity. Twosets of the contrast pulse sequence triplets [½e −1 ½o] provide a pairof complex values fed into the autocorrelators to generate a velocityestimate. Additional triplets can be used to increase the number ofpoints that are averaged, reducing the variance of the velocityestimates. By altering the transmit phase of triplets in a particularsequence, the velocity estimates for linear fundamental, secondharmonic, and cubic fundamental may be affected in useful ways.

The phase is altered between triplets or between combined triplets orother subset. Pulses of one sub-set of a sequence are transmitted with adifferent phase off-set than the pulses of another sub-set. The receivedsignals responsive to each sub-set are combined to obtain information atthe cubic fundamental. Each sample for velocity estimation correspondsto different sub-sets of pulses. The phase off-set is applied todifferent sub-sets of pulses. Where a pulse within a sub-set has a phaseoff-set relative to other pulses in the sub-set, the intra sub-set phaseoff-set is added to the sub-set phase off-set. The velocity is thenestimated from the resulting samples.

For example, phase shifts are applied to a 9-pulse sequence containingthree triplets. The phases applied to the three triplets are [0° 0°90°]. A 90° phase shift is applied to each of the pulses in the thirdtriplet and not to the pulses of the first two triplets. After combiningthe received signals for each triplet, three samples are input toestimate velocity. The first pair of complex samples fed to theautocorrelators has no relative phase change, so generate a normalvelocity estimate. The second pair of samples has a positive 90° phasechange for linear fundamental signals, 180° for second harmonic signalsand a 270° or −90° phase change for cubic signals. When this secondautocorrelation value or velocity estimate is averaged with the first,the true velocity from linear fundamental signals will see an average ofa 45° positive bias. The measured velocity is higher by ¼ of the Nyquistvelocity. The cubic fundamental has a bias of ¼ of the Nyquist velocityin the negative direction. The second harmonic has a zero bias, thefirst and second samples cancel each other out since they are ofopposite phase. The velocity has zero bias due to second harmonicclutter.

In one embodiment, the second harmonic is reduced by filtering in CPSimaging so that there is less energy to affect cubic fundamentalestimates. The filtering is performed by limiting axial bandwidth onreceive, which affects range resolution. There is a tradeoff betweensecond harmonic clutter and cubic fundamental bandwidth. In this phaseoff-set embodiment, by providing the relative phase off-sets, bias inthe velocity estimate due to second harmonic signals is reduced when theaxial bandwidth is broadened to include second harmonic signals.

More complete cancellation of information other than at the cubicfundamental is provided using a twelve pulse sequence with fourtriplets, each with transmit phasing of [0° 0° 120° 0°]. Three of thetriplets are associated with a same phase off-set and a fourth one ofthe triplets has a different phase off-set. Samples are obtained foreach of the triplets, such as each triplet including samplesrepresenting a same scan line. The velocity is estimated from thesamples, such as from four samples for each spatial location. Using foursamples, three complex correlated values are averaged by theautocorrelator. For fundamental frequencies, the velocities of thevalues to be averaged by the autocorrelators are shifted by [0° 120°−120°]. These sum to zero. The contribution of fundamental signal to theoverall velocity estimate is nil or reduced. For the second harmonic,the shift is [0° 240°−240°]. These also sum to zero. The contribution ofsecond harmonic signal to the velocity estimate is nil or reduced. Forthe cubic fundamental, the shift is [0 360° −360°] which is equal to [0°0° 0°]. These add constructively, resulting in a variance reductionbenefit. The velocity estimate value for non-accelerating objects ismostly or entirely determined by the cubic fundamental signal. Thevelocity estimates from this four triplet twelve pulse technique helpimprove the specificity of agent flow in moving tissue. Only or mostlycontrast agent signals produce a velocity estimate in non-acceleratingmoving tissue.

For the cases where large signals are from tissue (either harmonic orfundamental), the variance of the estimate may be used. For high energycases where velocities cancel out, the variance estimate(1-abs(R(1)/R(0)) may be quite high since R(1) is zero where R(1) andR(0) are the autocorrelation coefficients. A large variance indicatesclutter. The variance estimate is used to condition the display of lowvelocity signals with high energy. For example, one or both of theenergy and velocity is not used or reduced for high variance conditions.This suppression may further remove signals from tissue.

Other sequences with phase off-sets using triplets or other groupings ofCPS pulses may be used. For example, other phase sequences for a3-triplet, 9-pulse sequence with transmit phase adjustments arepossible. With a [0 45 0] phase adjustment, the two velocity estimatevalues each have a phase shift proportional to the harmonic order: [+45−45] fundamental (sums to zero bias), [+90 −90] second harmonic (sums tozero complete rejection) and [+135 −135] cubic (sums to a 180° bias). Asanother example in a [0 60 0] phase adjustment, the two velocityestimate values each have the following phase shifts: [+60 −60]fundamental (sums to zero bias), [+120 −120] second harmonic (sums to180° bias) and [+180 −180] cubic (sums to zero). This sequence rejectsor reduces velocities from the cubic fundamental signal, so may be usedto isolate parameters from the second harmonic signal.

In one embodiment of the CPS transmissions of act 30, the difference inamplitude of the transmitted pulses used to obtain information at thecubic fundamental is obtained by using different amplification orvoltages. In other embodiments, the difference in amplitude is obtainedby adjusting the aperture or number of elements and element spacing usedfor transmission of the pulses. For example, three or more sets of CPSpulses are transmitted in a sequence for a scan line. Each of the setshas a same amplitude and phase pattern of pulses. At least four of thepulses used in the sequence are responsive to a respective at least fourdifferent apertures. Other numbers of apertures may be provided. Threeor more sets of received signals responsive to the three or more sets oftransmitted pulses are combined respectively into three or more samplesfor velocity estimation.

For a simple example using the same three apertures for three sets oftriplets in a sequence, higher order filtering may be used to increasethe rejection of moving fundamental signals. The ½ −1 ½ set of pulses isarrived at by turning particular elements on and adjusting the polarityor phase of the transmitted waveform from each element as given below intable 5.

TABLE 5 Full aperture − − − − − − − − ½ aperture (even) + + + + ½aperture (odd) + + + +This aperture pattern has the desirable property that each elementcontributes an equal amount of positive and negative signal to theoverall combined result. Each element within any of the apertures isused a same number of times as all of the other elements within any ofapertures. This helps cancel certain system and transducernon-linearity. Alternatively, any given element may be used in differentnumber of apertures for a sequence than another element. U.S. Pat. Nos.6,602,195 and 6,682,482 disclose various aperture combinations for CPSpulses. The same or different apertures may be used for each set ofpulses within a same sequence.

To achieve high order fundamental suppression and some cubic fundamentalsuppression, the following CPS set of [⅓ −1 1 −⅓] may be used. Thefollowing aperture function can be used to realize this set of pulses:

TABLE 6 ¾ aperture (even) − − − − − − ¾ aperture (odd) + + + + + + ¼aperture (odd) − − ¼ aperture (even) + +

Four different aperture patterns are used. An additional zero isprovided at DC for linear fundamental suppression. A single zero cancelsstationary cubic fundamental components. The specificity of movingagents detection may be improved.

In addition to the higher order aperture patterns discussed above,clutter filtering may be used to further enhance velocity estimation.For example, the adaptive clutter filter discussed above using longcorrelation intervals with high sampling rates is used in conjunctionwith the single cancellation zero available in the cubic fundamentalsignal space to more effectively separate moving agent from agent thatis stationary relative to the moving tissue.

Longer CPS pulse sets may reduce sensitivity at low agent velocities.The previously discussed technique of rejecting the clutter bias mightbe a better way to make use of additional pulses to improve agentdetection. This also has the variance reduction benefits to the velocityand energy estimates that come from averaging multiple autocorrelationsamples.

A fourth order fundamental canceller of another embodiment usingaperture weighting of amplitude has the following weights: [⅙ −⅔ 1 −⅔⅙]. The following aperture pattern can realize this by weighting thefunction [1 −4 6 −4 1]/8:

TABLE 7 ¾ aperture x x x x x x x x x x x x ½ aperture (even) x x x x x xx x ½ aperture (odd) x x x x x x x x ⅛ aperture (even) x x ⅛ aperture(odd) x xEach “x” indicates the usage of a given element in a particularaperture. This five-pulse sequence has five different aperture amplitudefunctions. Each element contributes a single positive and singlenegative phase to the overall summation.

Crosstalk considerations may necessitate larger groupings of elementssuch that at least 2 or 4 adjacent elements are in use at all times(i.e., each “x” or column in Table 7 represents 2, 3, 4 or other numberof adjacent elements). In higher order sequences four and five pulsescan replace the triplets discussed earlier.

An alternative method for combining sequences to improve rejection is toapply not only different phases but vary transmit amplitude weightsbetween triplets. Consider the following triplet: [½e −1 ½ o]. For a 9pulse sequence, three triplets with weights [½ 1 ½] are used. The actualtransmitted aperture sequence is [⅓−1 −⅓] may be used. include even andodd elements or groups of elements. The aperture pattern for thissequence could be the following:

TABLE 8 Full aperture − − − − − − − − ½ aperture (even) ± ± ± ± ½aperture (odd) ± ± ± ± ¼ aperture (even-even) + + ¼ aperture(even-odd) + + ¼ aperture (odd-even) + + ¼ aperture (odd-odd) + +The apertures labeled with both “+” and “−” are used twice, once withpositive phasing and once with negative phasing. This transmit sequenceputs additional zeros at FS/2 and at FS/6 for increased fundamentalcancellation. This could be helpful in very high clutter, shallow depthenvironments where the very low power signal of the ¼aperture canpenetrate, such as in transesophageal, intravascular applications orsmall animal imaging.

The triplet pattern is maintained so that within the group of 9 pulses,the values may be useful for other purposes. For example, the output ofeach triplet with appropriate receive weighting is obtained. Receiveweighting is used since two of the three sets are associated with a halfamplitude of the other set. A weight is applied to received signals orfinal samples of one, two or all three sets to equalize the amplitudecontribution within the sequence. These resulting sample values areapplied to the velocity estimator. The velocity estimate may be computedwith normal levels of fundamental clutter rejection. The energy estimatemay be computed with all 9 points with a higher level of fundamentalclutter rejection and agent specificity. When these energy and velocityvalues are combined for display, such as with the map show in FIG. 3,the velocity is only displayed for signals with a high detected energy.

Contrast pulse sequence triplets or other sets of CPS pulses used in asequence can be corrected by inserting a preamble pulse, represented asan initial additional pulse within the triplet: [½o ½e −1½o]. Theamplitude and phase of the preamble or reverberation pulse is selectedso that first three values sum to zero. This ensures cancellation oflinear fundamental reverb signals. Techniques to determine the phase andamplitude of the reverberation suppression pulse are disclosed in U.S.Pat. No. 6,436,041, the disclosure of which is incorporated herein byreference. A second reverb pulse may be added as an initial negative onevalue: [−1 1/2o ½e −1½o].

The reverb pulse or pulses generates a similar acoustic environment foreach of the first pulses used in a combination to obtain a sample at thecubic fundamental. In an interleaving embodiment, each triplet (or othersub grouping) has a separate reverb firing. A 6-pulse sequence of twotriplets without reverb cancellation uses an 8-pulse sequence forreverberation cancellation. For example, with a flow sample interleaveratio (FSIR) of four, 4×6=24 firings without reverb pulses has 4×8=32firings with reverb pulses. Without a reverb pulse, the sequences forfour lines are: 1 1 1 2 2 2 3 3 3 4 4 4 1 1 1 2 2 2 3 3 3 4 4 4. Withthe addition of one reverb firing per triplet, the sequences are: 1 1 11 2 2 2 2 3 3 3 3 4 4 4 4 1 1 1 1 2 2 2 2 3 3 3 3 4 4 4 4, where eachtriplet includes one initial reverb pulse. The superscripts denoting theaperture, phase and/or polarity function are omitted for clarity.

If there are not large phase changes between lines, then earliertriplets may serve as reverb pulses for subsequent triplets. A 9-pulsesequence may then become a 10-pulse sequence after a single reverbcorrection pulse is added to the beginning of the sequences. Thisassumes no phase changes between the groupings. If phase changes occur,then additional reverb pulses may be used. The time between firing eachpulse is carefully controlled so that reverb pulses present theappropriate phase. In one embodiment, uniform pulse timing is used tocontrol the phase.

One other way to reduce the number of reverb lines is by allowing someinterleaving within triplets. For example, if the FSIR=4 with a twotriplet six-pulse sequence, the following 24 firing pulses are provided:1 2 1 2 1 2 3 4 3 4 3 4 1 2 1 2 1 2 3 4 3 4 3 4. Inserting single reverbpulses before each interleave triplet group provides 28 firings with thefollowing sequences: 2 1 2 1 2 1 2 4 3 4 3 4 3 4 2 1 2 1 2 1 2 4 3 4 3 43 4. One reverb pulse for each interleaved triplet pair is provided,reducing the number of reverb pulses from the previous case by 50% (from8 to 4). The contrast pulse sequence is acquired with a lower samplingrate (because of the interleaving) but a still longer correlationperiod. The lower sampling rate may introduce motion artifact due toimperfect cancellation of the fundamental signal.

The reverberation cancellation technique of using dead time before thetriplet, i.e. [0 ½e −1½o], may be used. However, reflections from thefirst transmitted pulse from objects deep in the body may be seen whenthe second pulse is being received. Reflections from the second pulsemay be seen on the third receive pulse. The first received pulse has noreflected signal. The three received pulses are combined with an FIRfilter—in this case a [1 1 1] filter. The missing reflection on thefirst pulse may prevent cancellation of the linear fundamental signalfrom the deep objects. If the object is a bright reflector, such as thediaphragm, then the contrast agent detector will register a largesignal. An example alternating polarity set of pulses without and withreverb pulses is provided as:

TABLE 9 Tx Sequence: ½ e −1  ½o Reverb Signal: ½ e −1 Rx weights: 1 1  1→ Reverb Sum: −1 + ½e = −½o Tx Sequence ½o ½e −1 ½o Reverb Signal: ½o ½e−1 Rx weights: 1  1  1 → Reverb Sum: −1 + ½e + ½o = 0An example uniform polarity sequence without and with reverb pulses isprovided as:

TABLE 10 Tx Sequence: ½ e 1 ½o Reverb Signal: ½ e 1 Rx weights: 1 −1  1→ Reverb Sum: 1 − ½e = ½o Tx Sequence −½o ½e 1 ½o Reverb Signal: −½o ½e1 Rx weights: 1 −1  1 → Reverb Sum: 1 − ½e − ½o = 0

An alternative to reverb suppression pulses is to increase the timebetween firing each pulse with the commensurate tradeoff on linearfundamental clutter suppression and reduction in frame rate. Theduration increase is between each of the firings.

The velocity scale may be adjusted to account for the sequencesdiscussed herein with or without reverberation. Velocity estimates areobtained using one of different possible sequences of pulsescorresponding different possible pulse repetition intervals. Forexample, the sequence is selected automatically in response to a type ofexamination or is selected as a function of user input. In response tothe selection of a specific sequence and associated pulse repetitioninterval, a velocity scale annotation is adjusted as a function of thepulse repetition interval. One way to implement this could be to have afilter dependent scale factor for the velocity scale, such as a scalefactor for multiplying the velocity scale used for annotation andcalipers. The velocity scale is based on a particular PRI. By using theDoppler equation, Nyquist velocities are computed. For these variouspulsing techniques, the velocity scale may have to be scaled (reduced)by integer factors which depend on the particular sequence. For example,the five pulse [½ −1 ½ −1 ½] set of CPS pulses has a true velocity scalewhich is one half as large. The six pulse set of CPS pulses is scaled by⅓. Other sequences may require different scale factors.

In act 30, each of the pulses within a sequence is transmitted along asame scan line. Where interleaving between scan lines is used, thepulses of a plurality of sequences are transmitted along a respectiveplurality of scan lines. Table 11 below shows an acquisition patternwith three firings per detected line (i.e., set of CPS pulses forsamples along a scan line). Linear fundamental suppression is providedby the second difference [1 −2 1] response.

Ultrasound Line

TABLE 11 T ½e i −1 m ½o e ½e ↓ −1 ½o ½e −1 ½o ½e −1 ½o L₀ L₁ L₂ L₃L_(n) indicates the scan line.

In alternative embodiments, one or more pulses within a set of CPSpulses for forming samples along a scan line or within a sequence ofmultiple sets include at least one pulse transmitted along one line andanother pulse transmitted along an adjacent line. For example, twopulses per detected scan line are used, resulting in linear fundamentalsuppression. Pulses are shared between scan lines or sequences. Thelines are not collocated so there may be linear fundamental leakage.Phase correction and good sampling density may be used to improve linearfundamental cancellation. Table 12 shows this first alternative:

TABLE 12 ½e −1 ½o −1 ½e −1 ½o −1 ½e L₀ L₁ L₂ L₃Some pulses are transmitted along scan lines located between the scanlines of interest.

In another alternative shown in table 13, only one pulse on average perdetected line is used. Poor linear fundamental suppression may beprovided. The second difference [1 −2 1] response is provided for linesL₀, L₃, L₆, etc., but the transmitted pulses within a set of pulses arenot collocated, resulting in linear fundamental leakage. A linearfundamental suppression response for other lines (L₁, L₂, L₄, L₅, etc)may be worse than first difference performance [1 1-2]. Line by linevariation in linear fundamental suppression performance may produceartifacts in the final image. Lateral video filtering may help suppressthe artifacts, trading off lateral resolution.

TABLE 13 ½e −1 ½o ½e −1 ½o ½e −1 ½o L₀ L₁/L₂ L₃ L₄/L₅ L₆The L₁/L₂ represents a scan line between L₀ and L₃. Samples are formedfor each of L₀-L₆. FIG. 5 shows a frequency response of the linearfundamental suppression using the pulses of Table 13. The solid linerepresents the L₁ and L₂ response, the dot-dash line represents the L₃response and the dotted line represents a first difference response forreference.

Table 14 represents yet another alternative transmit pattern. An averageof 2 firings per detected line are used for linear fundamentalsuppression based on the second difference [1-2 1] response. The scanlines are not collocated so there may be linear fundamental leakage.

TABLE 14 ½e −1 ½o −1 ½e −1 ½o −1 ½e −1 ½o L₁ L₂ L₃ L₄ L₅

Rather than estimating velocity or energy from samples representing thesame spatial locations, the number of pulses may be decreased byestimating from adjacent spatial locations. Consider a CPS set of pulseswhere triplets are processed to produce linear fundamental suppressedcomplex values Y_(n), such as shown in Table 15.

TABLE 15 ½e −1 ½o ½e −1 ½o ½e −1 ½o ½e −1 ½o Y₀ Y₁ Y₂ Y₃The complex autocorrelation value for line n is represented as:R(1)_(n)=Y_(n)Y_(n-1)* which correlates two complex values fromdifferent spatial scan lines. The velocity estimate for line n is then∠R(1)_(n). The velocity estimates may be obtained with only 3 pulses perline. Additional averaging could be performed:

${R(1)}^{n} = {\sum\limits_{k = n}^{n + 1}{Y_{k}Y_{k - 1}^{*}}}$

to reduce the variance of the velocity estimate as well as adjust thespatial center of mass of the velocity estimates for these lines.

Other techniques may also be applied. For example, the transmit phasesof consecutive triplets in adjacent lines can be modulated to helpreduce the linear fundamental signal velocity bias. In one embodiment,twelve pulses of a sequence may be realized with a 9 pulses per scanline. Each entry in table 16 represents a 3-pulse CPS triplet acquiredat a particular line Y.

TABLE 16 0° 0° 120° 0° 0° 120° 0° 0° 120° 0° 0° 120° Y₀ Y₁ Y₂ Y₃Three triplets acquired along a particular line (Y₁) are combined with asingle triplet acquired from an adjacent line (Y₂) to form a singlevelocity estimate with reduced bias from linear fundamental and secondharmonic clutter bias. The lines are close enough together to allow areasonable velocity estimate to be made across lines, such as beingadjacent scan lines.

The twelve pulse cancellation technique of the example embodiment abovemay be alternatively realized with an average of 1.5 triplets or 4.5pulses per line. In the following table 17, each row representscollinear firings of the [½e −1 ½o] contrast pulse sequence triplet.Each angle represents a transmit phase adjustment for all firings of aparticular triplet.

TABLE 17 0° 120° 0° 0° 120° 0° 0° 120° 0° 0° Y₀ Y₁ Y₂/Y₃ Y₄ Y₅/Y₆ Y₇ Y₈V₀ V₁ V₂ V₃ V₄The velocity values, V, are estimated based on the samples for each scanline, Y. For example, the velocities are estimated asV₀=∠Y₁Y₀*+Y₂Y₁*+Y₃Y₂* and V₁=∠Y₂Y₁*+Y₃Y₂*+Y₄Y₃*.

FIG. 4 shows one embodiment of a flow chart diagram of anotherembodiment of a method for contrast agent ultrasound imaging with cubicfundamental information. Additional, different or fewer acts may beused, such as including any of the acts of FIG. 2 or related pulses,sets of pulses or sequences with or without interleaving. The method isimplemented using the system of FIG. 1 or another system.

In act 40, a sequence of pulses is repetitively transmitted along a scanline. The sequence is free of interleaving in one embodiment. Forexample, the sequence is a set of pulses for obtaining one sample foreach spatial location. By transmitting CPS pulses, the sequencecorresponds to detection of cubic fundamental information. In oneembodiment, the pulse sequence represented as ½e −1 ½ is repeatedcontinuously.

In act 42, the received signals responsive to each repetition arecombined. The combination of received signals corresponding to each setor sequence provides cubic fundamental information. The receive signalsfrom each pulse of a triplet are added together in one embodiment.

In act 44, a fast Fourier transform (FFT) is performed as a function ofthe combined received signals from a plurality of the repetitions oftransmission and combination. The samples are continuously fed into anFFT. The measurement PRI (the display velocity scale) is 3× the actualPRI. The two zeros may remove most of the linear fundamental clutter.Reverberation is handled naturally because each pulse of the sequenceserves as natural reverb pulses for subsequent pulses. An initialreverberation pulse may or may not be used.

In act 46, an image responsive to the FFT is generated. The image is apulsed wave (PW) Doppler image for a gate location along the scan line.Since the cubic fundamental information is used for the PW Dopplerimage, imaging flow in coronary arteries may benefit. The cubicfundamental information has high contrast agent specificity and lowclutter. The lower clutter levels may also improve automatedquantitative measurements.

In one embodiment, act 40 is performed using a high pulse repetitionfrequency (PRF). Sequential transmissions are performed with a lesserdelay between transmissions. The delay may even be such that a secondtransmission is performed prior to an end of a time of flight for alocation of interest for a first transmission. High PRF may provide goodhigh velocity estimates with less concern for ghost gates being nearstrong clutter. Very low velocity scales may be used, and flows thatwould normally be obscured by clutter may be measured.

In some applications, such as coronary flow reserve studies, timinginformation is important. It is possible to create multiple Dopplerstrips. One strip is from data from the −1 transmit pulses andrepresents the fundamental signal energy containing significant tissuemotion. Tissue motion provides heart cycle timing information (i.e. thestart of systole and diastole). The other strip provides the cubicfundamental sensitive signal which is highly specific to the movingcontrast agent. The two strips may also be stacked one on top of theother on the display or overlaid with different colors. The two stripsmay have the same or different effective measurement PRIs. Thefundamental pulses may be sub-sampled to get a PRI that is an integermultiple longer for the fundamental strip than for the cubic fundamentalstrip. The receive weights and phases may be altered from the ½e and ½opulses so that all pulses can be used for a fundamental sensitive stripand a shorter measurement PRI can be used. Since tissue timinginformation is of interest, clutter leakage from imperfect cancellationmay be less of a concern.

Cubic fundamental velocity, energy, intensity and/or other type ofinformation is used for three-dimensional imaging in one embodiment. Toreduce scan time or frame rate, different pulses are transmitted alongdifferent lines in a volume. The CPS pulses to form samples along a scanline are transmitted along a same or different scan lines. Table 18shows a 2 dimensional sampling pattern of CPS triplets acquired in orderfrom 1-16 for a total of 16×3=48 line firings:

TABLE 18 1 3 5 7  9 11 13 15 2 4 6 8 10 12 14 16In one embodiment, these triplets are acquired with the transmit phaseangles shown in table 19:

TABLE 19 0 120 0 0 120 0 0 120 0 0 120 0 0 120 0 0The velocity estimates are formed with samples for 4 triplets of 7 scanlines centered at each group of four. Groups of 4 lines are combined inone embodiment as shown in Table 20.

TABLE 20 Line combination phase sequence 1, 2, 3, 4 0, 0, 120, 0 3, 4,5, 6 120, 0, 0, 120 5, 6, 7, 8 0, 120, 0, 0 7, 8, 9, 10 0, 0, 120, 0 9,10, 11, 12 120, 0, 0, 120 11, 12, 13, 14 0, 120, 0, 0 13, 14, 15, 16 0,0, 120, 0These phase sequences have 0, +120 and −120 degree phase differences indifferent orders. The phase differences produce fundamental cluttervelocity bias cancellation. The average number of pulses to acquirethese 7 scan lines is 48÷7≈6.9 firings.

The energy estimates are formed with a higher spatial sampling densitythan the velocity estimates. Each energy estimate may be formed from asingle set of pulses, resulting in a greater sampling density. Spatialfiltering operations to smooth out artifacts can be set to account forthe different parameter sampling densities. For example, the spatialsmoothing coefficients are varied to increase the amount of smoothing ofthe higher density energy estimates to reduce speckle and reduce theamount of smoothing of the lower density velocity estimates. Thesmoothing equalizes the actual resolution after reconstruction betweenthe velocity and energy estimates.

A three-dimensional image is generated as a function of the cubicfundamental transmissions and received signal combinations. Any detecteddata may be used for generating the image. Where both velocity andenergy estimates are used, the different in sampling grid is accountedfor in scan conversion and/or in the 3D reconstruction.

Volume flow measurements before and after drug or exercise challengesare useful in clinical determinations of heart health. Cross sectionalarea measurements in 2D images are problematic due to unknown vesselorientation. Clutter is also a serious limitation to mean velocitycomputation. In practice, the maximum velocity waveform is used andrelative measurements are made before and after cardiac challenge toderive coronary flow reserve. Contrast agent flow in coronary arteriesin 3D is shown with a high degree of specificity to actual blood flow bythe cubic fundamental information (rejecting fundamental clutter).Vessel cross sectional area measurements (derived from the cubicfundamental 3D vessel image) may be combined with mean velocityinformation (again derived from the cubic fundamental signals frommoving agent) to compute volume flow. Volume flow changes before andafter challenge may be clinically useful. Since there are smallvariations in the size of the coronary artery before and afterchallenges, it may be sufficient to use the time integrated meanvelocity waveform in clinical comparisons. This may provide betteraccuracy over the maximum velocity waveform. The rejection of tissueclutter provided by the cubic fundamental agent information enables themean waveform to be used.

FIG. 6 shows another embodiment of a method for contrast agentultrasound imaging with cubic fundamental information. Additional,different or fewer acts may be used, such as including any of the actsof FIG. 2 or 4 or related pulses, sets of pulses or sequences with orwithout interleaving. The method is implemented using the system of FIG.1 or another system.

In act 50, cubic fundamental information is detected. Any of the CPStechniques discussed above may be used. The detected data may includeonly cubic fundamental information or information in addition to thecubic fundamental. The detected cubic fundamental information isdetected at one or more spatial locations, such as along twointersecting lines or for each of a plurality of locations in a regionat two different times

In act 52, one or more motion estimation techniques are performed. Forexample, one or both of acts 54 and 56 are performed. Acts 54 and 56correspond to obtaining directional velocity information, either of oneframe of data relative to another frame of data or of amulti-dimensional velocity vector for a given spatial location. Othermotion estimation techniques different than one dimensional velocity orenergy detection may be used. The techniques take advantage of theclutter rejection and/or other characteristics of the cubic fundamentalinformation. The linear fundamental clutter rejection available from theCPS triplet and the specificity to cubic fundamental signals allows anumber of motion estimation techniques to be more likely to succeed. Forexample, the techniques of spatial quadrature, cross correlation, andspeckle tracking all have serious limitations due to clutter. Operatingthese techniques on clutter free cubic fundamental signals allow morepractical use of these techniques. Lateral velocity estimation may bemore accurate without clutter. Low velocity information without clutterby detecting the cubic fundamental may be possible without frame ratereduction due to large clutter filters.

In act 56, a directional velocity estimate is obtained. For example, atwo or three-dimensional velocity is obtained. In one embodimentrepresented in FIG. 7, cubic fundamental information is obtained alongtwo intersecting scan lines 60. Velocity estimates at the point ofintersection provide velocity information in each of the two differentscan line directions. The geometric relationship of the scan lines maybe used to determine a two-dimensional velocity. For cross-beamdetection methods low lateral spatial-frequencies/velocities remain andvector estimates become more accurate, especially for velocitiespredominantly in the x-direction. A three dimensional velocity vectormay be derived from three intersecting beams or the tracking of specklebetween two acquired volumes with the use of a 2D transducer array. A 3Dvelocity vector may also be derived from two separate two-dimensionalvelocity vectors from orthogonal planes within a volume.

In act 54, speckle tracking is performed. FIG. 8 shows speckle trackingbetween the two different times where “X” indicates data from one frameof data and “O” indicates data from a different frame of data. Thespatial locations marked “X” are a region of interest or speckleinformation to be tracked. By tracking the region from one frame toanother frame, the relative motion of the region is determined. Beforetracking the velocity using the target region within a search region(e.g., locations labeled with “O”), clutter is removed. A flow samplecount (i.e., the number of firings to a same location) number of pulsesare acquired per line L_(i) (i=1, 5). By using cubic fundamentalinformation, a simple or no clutter filter may be used to remove clutterinformation. Correlation, sum of absolute differences or othercalculation is used to determine a sufficient match of translationand/or rotation of the target region to the search region.

Before tracking the velocity using the target region within a searchregion, clutter is removed. Pulses are acquired per line L_(i) (i=1, 5)and filtered with T taps/coefficients of the clutter filter. For lowvelocity detection, a clutter filter with more than three coefficientsis used so the transition band between the stop band and the pass bandis narrow and strong clutter signals may not override the weaker bloodsignals. Using the following ‘minimal’ example with a flow sample countof 4 (FSC=4) and T=4, the frame rate is primarily determined bytransmitting (4×5)+(4×3)=32 pulses. If the pulses where acquiredsequentially in space across lines L_(i) and then repeated to build upthe FSC number of pulses per line, the number of filter coefficients isgreater than 4 for the same minimum detectable velocity since more timeexists between pulses filtered by the clutter filter. This latteralternative reduces frame rates even further. For speckle-trackingmethods, low lateral velocities also remain and in addition lesstransmit pulses are required. Since only a minimum of three pulses arerequired per line in each of the target and search regions, the totalnumber of pulses in the example above drops to (3×5)+(3×3)=24 instead ofthe 32 pulses. For detecting even lower velocities, the improvement inframe rate may be greater given the need for a larger number of clutterfilter coefficients and therefore more transmit pulses beyond 4 perline.

For each line in the cross-beam, speckle-tracking, or other method ofdetecting vector motion, N pulses are fired as fast as practical andcombined appropriately to suppress linear fundamental energy and detectcubic fundamental. This step for each line effectively eliminates orreduces clutter, leaving nonlinear energy to be used for detectingstationary, slowly, or quickly moving blood or contrast agent. Sincethis step effectively separates clutter (at linear fundamentalfrequency) from the desired blood flow (at nonlinear fundamental),movement over a range of velocities can be detected and any significantbiases may be minimized.

While the invention has been described above by reference to variousembodiments, it should be understood that many changes and modificationscan be made without departing from the scope of the invention. It istherefore intended that the foregoing detailed description be regardedas illustrative rather than limiting, and that it be understood that itis the following claims, including all equivalents, that are intended todefine the spirit and scope of this invention.

1-31. (canceled)
 32. A method for contrast agent imaging withultrasound, the method comprising: (a) repetitively transmitting a firstsequence of first pulses along a first line, the first sequencecorresponding to detection of cubic fundamental information; and (b)combining received signals for each repetition of the first sequencetogether, the combination providing the cubic fundamental information;(c) performing a fast Fourier transform as a function of the combinedreceived signals from a plurality of the repetitions of (a); and (d)generating an image responsive to (c).
 33. The method of claim 32wherein (c) and (d) comprise generating a pulsed wave Doppler image fora gate location along the first line.
 34. The method of claim 32 wherein(a) comprises repetitively transmitting at a high pulse repetitionfrequency such that a second transmission is performed prior to an endof a time of flight for a first transmission. 35-37. (canceled)
 38. Themethod of claim 32 wherein (a) comprises deriving the cubic fundamentalfrom sequence where amplitude and phase change.
 39. (canceled)
 40. Themethod of claim 32 wherein generating the image comprises generating animage of multiple Doppler strips.
 41. The method of claim 40 wherein themultiple Doppler strips comprise a first strip for tissue motion and asecond strip for contrast agents.
 42. The method of claim 41 wherein thefirst strip has a different measurement pulse repetition interval thanthe second strip.
 43. The method of claim 42 wherein the first strip hasa longer pulse repetition interval than the second strip.
 44. The methodof claim 32 wherein transmitting the first sequence comprisestransmitting a plurality of pulses having at least two differentamplitude levels.
 45. The method of claim 32 wherein transmitting thefirst sequence comprises transmitting a plurality of pulses havingdifferent phases.
 46. The method of claim 45 wherein the pulses have atleast two different amplitude levels.